Apparatus and method for reduction of neurological movement disorder symptoms using wearable device

ABSTRACT

A multimodal wearable band which uses mechanical vibrations to stimulate sensory neurons in the wrist or ankle in order to reduce the severity of tremors, rigidity, involuntary muscle contractions, and bradykinesia caused by neurological movement disorders and to free users from freezing induced by movement disorders. The device uses sensors to provide output used by a processing unit to determine the optimal stimulation pattern for each user and to determine when stimulation is necessary, and then uses one or more vibration motors to accordingly stimulate the users neurological pathways to lessen the severity of a user&#39;s symptoms. The device can also be adapted to integrate with 3rd party devices.

PRIORITY

This patent application is a continuation of U.S. patent application Ser. No. 17/063,363, filed Oct. 5, 2020, which is a continuation-in-part of U.S. patent application Ser. No. 16/563,087, filed Sep. 6, 2019, which claims the benefit of U.S. provisional patent application Ser. No. 62/729,977, filed on Sep. 11, 2018, and U.S. provisional patent application Ser. No. 62/797,310, filed on Jan. 27, 2019. These applications are hereby incorporated, in their entirety, by reference.

TECHNICAL FIELD

The present invention relates to wearable medical devices and in particular to wearable medical devices that mitigate symptoms of neurological movement disorders.

BACKGROUND ART

There are a number of neurological movement disorders which exhibit a range of somewhat similar symptoms, examples of which follow. Essential tremor is characterized by tremor of the extremities. Parkinson's Disease (PD) can cause tremor, rigidity, bradykinesia, and temporary freezing or inability to begin a motion. Restless Leg Syndrome does not cause a tremor; however, it causes a strong compulsion to move and shake the patient's legs. Tremor can also be present as a side effect of certain medications.

There are approximately 10 million people living with Parkinson's Disease (PD) in the world today, and over 70% of these patients experience tremors—the involuntary trembling or shaking of the extremities. Other symptoms of PD include stiffness or rigidity of the muscles, bradykinesia (defined as slowness of movement), and freezing (defined as the temporary, involuntary inability to move).

Parkinson's Disease has no cure. Treatments at the moment consist of medications to address patients' symptoms, though these do not reverse the effects of the disease. Patients often take a variety of medications at different doses and different times of day to manage symptoms. PD medications are most often dopaminergic, either supplying or mimicking the effects of dopamine to replenish the depleted dopamine state caused by the disease.

Surgical procedures can be prescribed for patients who have exhausted their medical treatment options. The first method of surgical treatment is Deep Brain Stimulation (DBS). In this procedure, electrodes are inserted into the brain, and then an impulse generator battery is implanted under the collar bone or in the abdomen. The patient uses a controller to power the device on or off, as needed, to help control tremors. DBS can be effective for both Parkinson's disease and essential tremor, but this procedure is incredibly invasive and expensive.

The second surgical procedure available for Parkinson's patients is Duopa therapy. Duopa therapy requires a small hole (a stoma) to be surgically made in the stomach to place a tube in the intestine. Duopa, which is similar to normal PD medications taken through pills, is then pumped directly into the intestine, which improves absorption and reduces off-times of medications taken by pill.

A similar disorder, called essential tremor, has an even higher incidence rate with an estimated 100 million cases worldwide. These tremors can get bad enough that patients no longer have the ability to cut their food, tie their shoes, or sign their name. Essential tremor medications can include beta blockers and anti-seizure medications. These medications are known to cause fatigue, heart problems, and nausea.

Restless Leg Syndrome (RLS) affects roughly 10% of the population in the United States. RLS can also be a side effect of primary Parkinson's Disease. RLS is characterized by unpleasant tingling sensations in the patient's legs. These sensations occur when the legs are still and are alleviated when the legs are in motion. As a result, RLS patients are compelled to move or shake their legs. This is particularly detrimental to the quality of patients' sleep as they are unable to remain still.

RLS is commonly treated by dietary changes, medications, and/or physical therapy. Dietary changes can include eliminating caffeine, alcohol, and tobacco. Medications prescribed for RLS can include the same type of medications prescribed for Parkinson's Disease (such as dopamine agonists and carbidopa-levodopa) and benzodiazepines (such as lorazepam, Xanax, Valium, and Ativan). Physical therapy for RLS can include massaging the legs or electrical or vibrational stimulation.

One example of a device that uses vibration to treat RLS is described in “Systems, devices, and methods for treating restless leg syndrome and periodic limb movement disorder,” Walter, T. J., & Marar, U. (2010), U.S. Patent Application Publication No. US20100249637A1. This device is a lower leg sleeve with sensors and actuators, but it does not store or transmit data, nor does it address any of the other symptoms common to neurological movement disorders.

There are also a number of pharmaceutical avenues for the management of neurological movement disorder that function by promoting dopamine, a chemical produced by the brain which helps control body movement. This chemical is lacking in the brains of patients with diseases such as Parkinson's disease. Pharmaceutical treatment for Parkinson's disease is expensive, costing users thousands of dollars annually, ineffective, wearing off quickly; and thought to actually accelerate neurodegeneration.

There also exists an injection-based Botox treatment for more severe tremors which costs tens of thousands of dollars annually and works by killing the nerves responsible for the tremors. This is effective in reducing the tremors, but the death of the nerves also causes a significant decrease in mobility. Additionally, this treatment is only available at very specialized treatment centers and therefore is not an option for the vast majority of patients.

There are a number of devices that attempt to control unwanted movement using surface-based treatment, but none have proven to be completely non-invasive and effective. Many have settled on electrical stimulation as their chosen mode of neurostimulation for the relief of unwanted movement. This can involve various equipment and inconvenient procedures such as get pads or electrodes that require shaving for proper attachment. See “Closed-loop feedback-driven neuromodulation,” DiLorenzo, D. J. (2014), U.S. Patent No. US8762065B2. These devices only work after the electrical treatment is concluded, and the effects have not been shown to last for extended periods of time, leading to the assumption that many of these inconvenient treatments must be administered throughout the day to maintain tremor reduction. See “Devices and methods for controlling tremor,” Rosenbluth, K. H., Delp, S. L, Paderi, J., Rajasekhar, V., & Altman, T. (2016), U.S. Patent No. X9452287B2; “Systems for peripheral nerve stimulation to treat tremor,” Wong, S. H., Rosenbluth, K. H., Hamner, S., Chidester, P., Delp, S. L., Sanger, T. D., & Klein, D. (2017), U.S. Pat. No. 9,802,041B2. The aforementioned treatment poses significant risk for patients with pacemakers, and has also been found to cause skin irritation. They provide benefit only for tremor and do not provide relief from other symptoms of neurological movement disorders, such as bradykinesia, freezing of gait, dystonia, dyskinesia, or involuntary or compulsive rhythmic movement.

Perhaps the most relevant studies have emerged in the last few years and demonstrate that using vibration may improve motor performance. It seems that there is much variation in efficacy, which depends on the frequency of vibration, as well as the patient's condition. Macerollo et al. demonstrated that 80 Hz peripheral tactile vibration may result in less slowing and a decrease in repetitive hand movement in “Effect of Vibration on Motor Performance: A new Intervention to Improve Bradykinesia in Parkinson's Disease?”, Macerollo A, et al., (2016), Neurology April 2016, 86 (16 Supplement) P5.366. For post-stroke patients, 70 Hz has proven effective. This is demonstrated by Conrad MO, et al., in two separate papers: “Effects of wrist tendon vibration on arm tracking in people poststroke,” Conrad M O, Scheidt R A, Schmit B D (2011), J Neurophysiol, 2011; 106(3) 1480-8; and “Effect of Tendon Vibration on Hemiparetic Arm Stability in Unstable Workspaces,” Conrad MO, Gadhoke B, Scheidt RA, Schmit BD (2015). PLoS ONE 10(12): e0144377. Even paretic muscles are proven to respond to frequencies between 150 and 160 Hz, and the effects of such vibration are seen in a lasting reduction in weakness and spasticity in the treated muscles. See “The effects of muscle vibration in spasticity, rigidity, and cerebellar disorders,” Hagbarth, K. E., & Eklund, G. (1968), Journal of neurology, neurosurgery, and psychiatry, 31(3), 207-13. There exists one device which provides haptic signals around a user's wrist using actuators positioned along a band. These actuators slide along the band to change location relative to one another in order to provide signals in the correct location, See “Wearable device,” Zhang, Haiyan, Helmes, John Franciscus Marie, Villar, Nicolas (2018), U.S. Patent No. US20180356890A1.

Therefore, there is a need for a device that non-invasively, reliably, and affordably relieves symptoms of neurological movement disorders.

Summary of the Embodiments

In accordance with one embodiment of the invention, a wearable device is provided for mitigating a set of movement disorder symptoms of a subject. The device includes a housing and an attachment system, coupled to the housing, and configured to be attached to a body part of a subject. The device further includes a set of body part sensors, disposed in the housing, to provide a set of sensor outputs related to movement of the body part. The device also includes a processing unit, disposed in the housing, and operationally coupled to the set of body part sensors. The processing unit is configured, through a feedback loop, to produce, based on the set of sensor outputs, a stimulation signal for mitigating the set of movement disorder symptoms. The processing unit includes: (i) a set of filters configured to remove, from the sensor outputs, noise unrelated to the movement disorder symptoms, and (ii) an active noise cancellation processor configured to (a) transform the sensor outputs into frequency data, (b) use the frequency data to determine a fundamental frequency of the movement disorder symptoms, (c) generate the stimulation signal by processing the sensor outputs based on the fundamental frequency; and (d) apply, to the stimulation signal, a time delay calculated based on the fundamental frequency. The device further includes a set of mechanical transducers, disposed in the attachment system and operationally coupled to the processing unit to provide a set of mechanical outputs. The processing unit is further configured to control the set of mechanical outputs to deliver the stimulation signal to the body part of the subject.

Optionally, the set of movement disorder symptoms is selected from the group consisting of tremor, rigidity, bradykinesia, dyskinesia, compulsion to move, and combinations thereof. Optionally, the processing unit is further configured to detect a freezing gait of a patient with Parkinson's Disease. Alternatively or additionally, the processing unit is further configured to control the set of mechanical transducers so as to relieve the freezing gait of a patient with Parkinson's Disease. Optionally, the processing unit is configured to operate in two modes, a first mode in which it is configured to monitor patent movements passively to detect a movement disorder symptom above a threshold and a second mode in which, following detection of such a movement disorder symptom, the processor is configured to enter into active mitigation of the movement disorder symptom.

Optionally, the attachment system includes a wristband, and the set of mechanical transducers are distributed throughout the circumference of the wristband. Optionally, the device is operated by a button on a face of the device, and the button is configured on the face to allow for ease of use by a patient whose fine motor control is affected by a neurological movement disorder. Optionally, the wristband is configured with a hook-and-loop fastener, such that the wristband can be fastened with a single hand for ease of use by those whose fine motor control is affected by a neurological movement disorder. Optionally, the wristband is configured to be expandable via elastic deformation for ease of use by those whose fine motor control is affected by a neurological movement disorder Optionally, the device further includes a battery, disposed on the house, and a magnetic connector coupled to the battery and mounted in the housing for coupling to a mating connector for an external charger, so that the battery can be conveniently configured for charging by a patient lacking fine motor control.

Optionally, the processing unit is further configured to store the data collected by the set of body part sensors in memory coupled to the processing unit.

Optionally, the active noise cancellation processor is configured to transform the sensor output into the frequency data by applying a Fourier Transform to the sensor output. Alternatively or additionally, the active noise cancellation processor is configured to: (i) select the fundamental frequency by applying an argmax function to the transformed sensor output and (ii) use a bandpass filter to remove, from the stimulation signal, a set of frequency data outside a specified range associated with the fundamental frequency.

Optionally, the set of body part sensors includes an inertial motion unit (IMU) configured to calculate data representing the body part's acceleration, and the active noise cancellation processor is further configured to: transform the body part's acceleration data to the frequency data by applying a Fourier Transform; extract peak frequencies of the body part's acceleration data from the frequency data; select a window size of the body pail's acceleration data based on the peak frequencies; and capture a portion of the sensor output based on the selected window sire and invert the captured portion to generate the stimulation signal. Alternatively or additionally, in selecting the window size, the active noise cancellation processor inverts a lowest of the peak frequencies and converts the inverted lowest of the peak frequencies into a time domain. Optionally or additionally, the active noise cancellation processor is configured to set the window size to a fixed value.

In accordance with another embodiment of the present invention, a method is provided for mitigating a set of movement disorder symptoms of a subject. The method includes sensing movement of a body part of the subject to provide a set of sensor outputs related to movement of the body part. The method also includes processing the sensor outputs to produce a stimulation signal for mitigating the set of movement disorder symptoms. The processing includes filtering the sensor outputs to remove noise unrelated to the movement disorder symptoms so as to produce a filtered signal. The processing also includes actively processing the filtered signal to (a) transform the sensor outputs into frequency data, (b) use the frequency data to determine a fundamental frequency of the movement disorder symptoms, (c) generate the stimulation signal by processing the sensor outputs based on the fundamental frequency; and (d) apply, to the stimulation signal, a time delay calculated based on the fundamental frequency. The method further includes inputting the stimulation signal to a set of mechanical transducers coupled to the body part so as to mitigate the set of movement disorder symptoms.

Optionally, the set of movement disorder symptoms is selected from the group consisting of tremor, rigidity, bradykinesia, dyskinesia, compulsion to move, and combinations thereof. Optionally, sensing movement of a body part includes operating in two modes, a first mode that monitors patent movements passively to detect a movement disorder symptom above a threshold and a second mode that, following detection of such a movement disorder symptom, enters into active mitigation of the movement disorder symptom. Optionally, actively processing the filtered signal to transform the sensor outputs into frequency data includes applying a Fourier Transform to the sensor output. Alternatively or additionally, actively processing the filtered signal to transform the sensor outputs into frequency data includes: (i) selecting the fundamental frequency by applying an argmax function to the transformed sensor output and (ii) using a bandpass filter to remove, from the stimulation signal, a set of frequency data outside a specified range associated with the fundamental frequency.

Optionally, the sensor outputs to produce the stimulation signal further includes calculating data representing the body part's acceleration; transforming body part's acceleration data to the frequency data by applying a Fourier Transform; extracting peak frequencies of the body part's acceleration data from the frequency data: selecting a window size of the body pan's acceleration data based on the peak frequencies; and capturing a portion of the sensor output based on the selected window size and invert the captured portion to generate the stimulation signal. Alternatively or additionally, selecting the window size includes inverting a lowest of the peak frequencies and converting the inverted lowest of the peak frequencies into a time domain. Alternatively or additionally, selecting the window size includes setting the window size to a fixed value.

BRIEF DESCRIPTION OF THE DRAWINGS

The foregoing features of embodiments will be more readily understood by reference to the following detailed description, taken with reference to the accompanying drawings, in which:

FIG. 1 illustrates a system for mitigating movement disorder in accordance with an embodiment of the present invention.

FIG. 2 is an electrical schematic highlighting the main sub-circuits of the system in FIG. 1 .

FIG. 3 is an isometric view of a wearable device in accordance with an embodiment of the present invention.

FIG. 4 is an exploded isometric view of a wearable device, in which the vibration motors are housed in the band rather than in the main electronics housing, in accordance with an embodiment of the present invention.

FIG. 5 is an isometric view of a wearable device, in which the device includes a loop mechanism to allow single handed adjustment of the band on the user's wrist, in accordance with an embodiment of the present invention.

FIG. 6 shows an embodiment of the present invention worn on a hand viewed from above.

FIG. 7 shows an embodiment of the present invention worn on a hand viewed from the side.

FIG. 8 shows a testing configuration for the wearable medical device, which may be used for more rigorous data collection, in accordance with an embodiment of the present invention.

FIG. 9 illustrates a wearable device for mitigating movement disorder, in which the device is an accessory to a third-party smartwatch or other wearable computing device, in accordance with an embodiment of the present invention.

FIG. 10 shows a side view of a wearable device, which is as an accessory band for a third-party smartwatch or other wearable computing device, in accordance with an embodiment of the present invention.

FIG. 11 shows a process by which a raw sensor input is used to compute a set of stimulation parameters, in accordance with an embodiment of the present invention.

FIG. 12 shows a feature extraction process, in accordance with an embodiment of the present invention.

FIG. 13 shows a stimulation optimization algorithm, in accordance with an embodiment the present invention.

FIG. 14 shows a neurological signal cancelling system, illustrating how the wearable device and body interact, in accordance with an embodiment of the present invention.

FIG. 15 shows a process in which the raw sensor input may be processed using active noise cancellation to compute a set of stimulation parameters, in accordance with an embodiment of the present invention.

FIG. 16 shows one exemplary embodiment of the process of anti-tremor stimulation signal generation by the active noise cancellation (ANC) processor.

FIG. 17 shows another exemplary embodiment of the process of anti-tremor stimulation signal generation by the ANC processor.

FIG. 18 is a pair of renderings by a Parkinson's patient of a spiral under conditions without and with treatment by a device in accordance with an embodiment of the present invention.

FIG. 19 illustrates an embodiment of a simple non-convex gradient descent optimization used in embodiment of the present invention for symptom reduction by searching over the parameter configuration space.

FIG. 20 shows a power spectral density (PSD) plot of the postural tremor of a Parkinson's Disease patient with and without the use of a device in accordance with an embodiment of the present invention.

FIG. 21 shows a power spectral density (PSD) plot of the postural tremor of an Essential Tremor patient with and without the use of a device in accordance with an embodiment of the present invention.

DETAILED DESCRIPTION OF SPECIFIC EMBODIMENTS

Definitions. As used in this description and the accompanying claims, the following terms shall have the meanings indicated, unless the context otherwise requires-.

A “set” includes at least one member.

A “body part” is a part of a human body, such as a limb (examples of which include an arm, a leg, an ankle, and a wrist) or the neck.

A “body part sensor” is a sensor responsive to a parameter, associated with a body part, the parameter selected from the group consisting of force, motion, position, EMG signal directed to a set of muscles of the body part and combinations thereof.

A “mechanical transducer” is a device having an electrical input and a mechanical output configured to provide physical stimulation to a subject.

A “movement disorder sensor” is a sensor that is configured to provide a measurement associated with a neurological movement disorder.

An “attachment system” is a system or a device having a means to mechanically affix component subsystems to the user's person.

A “housing” is a primary enclosed casing which contains one or more component subsystems.

A “band” is a flexible segment of material which encircles a body part or portion of a body part for the purpose of affixment which may also house one or more component subsystems.

The term “vibrational stimulus” refers to a vibration or series of vibrations produced by a vibration motor or group of vibration motors embedded in the device. These vibrations are used to stimulate a response from the targeted proprioceptors in the user's body.

The term “stimulation pattern” refers to a vibrational stimulus which is characterized by a number of parameters including frequency, amplitude, and waveform. A “stimulation pattern” can also refer to a longer time scale behavior over which the above-mentioned parameters evolve over time.

The term “proprioception” refers to the sense of the position of one's own limbs or body parts and the intensity of force being applied through that body part. A proprioceptor is a sensory neuron which is used for proprioception. There are two types of proprioceptors “muscle spindles” which are located in the muscle and the “Golgi tendon organs” which are located in the tendons.

The term “neurological movement disorder” refers to any of the neurological conditions that cause abnormally increased or decreased movements which may be voluntary or involuntary. These include but are not limited to: Ataxia, cervical dystonia, chorea, dystonia, functional movement disorder, Huntington's disease, multiple system atrophy (MSA), paresis, hemiparesis, quadriparesis, post-stroke movement disorders, myoclonus, Parkinson's disease (PD), Parkinsonism, drug induced Parkinsonism (DIP), progressive supranuclear palsy (PSP), restless legs syndrome (RLS), tardive dyskinesia, Tourette syndrome, spasticity, rigidity, bradykinesia, tremor, essential tremor (ET), alcohol or drug withdrawal induced tremor, drug induced tremor, psychogenic tremor, rest tremor, action tremor, cerebellar lesion, rubral tremor, isometric tremor, task-specific tremor, orthostatic tremor, intention tremor, postural tremor, periodic limb movement disorder, and Wilson's disease.

The term “training period” refers to a period or phase of the device's operation during which the device is conducting experimentation or collecting and analyzing data for the purpose of deducing the optimal stimulation pattern.

A “computer process” is the performance of a described function in a computer system using computer hardware (such as a processor, field-programmable gate array or other electronic combinatorial logic, or similar device), which may be operating under control of software or firmware or a combination of any of these or operating outside control of any of the foregoing. All or part of the described function may be performed by active or passive electronic components, such as transistors or resistors in using the term “computer process” we do not necessarily require a schedulable entity, or operation of a computer program or a part thereof, although, in some embodiments, a computer process may be implemented by such a schedulable entity, or operation of a computer program or a part thereof. Furthermore, unless the context otherwise requires, a “process” may be implemented using more than one processor or more than one (single- or multi-processor) computer.

The present invention is directed generally towards wearable medical devices and in particular towards the mitigation of tremors, rigidity, bradykinesia, involuntary rhythmic movements, and freezing associated with neurological movement disorders through mechanical vibrational stimulation of the tendon bundles in the wrist and autonomous sensing, feedback, and adjustment. There are also a number of considerations taken into the embodiment of the device which facilitate ease of use by the disabled populations for whom the invention is intended, including integration with 3rd party devices.

Embodiments of the present invention include systems and methods of treating symptoms of neurological movement disorders by stimulating proprioceptors. In some embodiments, the systems are wearable devices. In some embodiments, the systems and methods can be used for any neurological movement disorder, including but not limited to Parkinson's Disease, Essential Tremor, post-stroke movement disorders, or Restless Leg Syndrome. In some embodiment, the symptoms treated include tremor, rigidity, bradykinesia, stiffness, hemiparesis, and freezing. In some embodiments, the symptoms treated include muscle contraction caused by dystonia. In some embodiments, the symptoms treated include the inability to locate one's limbs in space. In some embodiments, the proprioceptors targeted for stimulation are located in the wrist. In some embodiments, the proprioceptors targeted for stimulation are located in the ankle. In some embodiments, the proprioceptors targeted for stimulation are located in the neck.

In some embodiments, the systems provide stimulus to the proprioceptive nerves (proprioceptors) for reducing symptoms by the use of vibration motors positioned around the surface of the wrist. In some embodiments, the systems cycle through frequency patterns and waveforms of stimulation to find the pattern that results in the greatest reduction of movement disorder symptoms. In some embodiments, the systems use random white-noise subthreshold stimulation in order to leverage the effect of sensory stochastic resonance. In some embodiments, the systems are coupled to one or more sensors that measure the user's tremor for each of a set of possible stimulation patterns, and the systems assign the pattern of stimulation that relates to the biggest measured decrease in tremor amplitude of that user relative to the tremor exhibited in the absence of stimulation

In some embodiments, the device finds (learns) the optimal stimulation parameters for use in reducing the symptoms by using sensor-based optimization, including but not limited to model free reinforcement learning, genetic algorithms, Q-learning. These parameters can include any quantities used to define a stimulation waveform such as frequency, amplitude, phase, duty cycle, etc. In some embodiments, these learned parameters also describe the longer time scale behavior of the stimulation pattern evolving over time. In some embodiments, the device determines the optimal stimulation as the weighted average of the optimal stimulations for each of the independent symptoms observed where the weights are proportional to the symptom severity relative to the other observed symptoms. For example, if the patient experienced tremors and rigidity, and the severity of the tremors was double that of the rigidity, the output stimulation would be two times the optimal tremor reducing pattern superposed with one times the optimal rigidity reducing pattern in some embodiments, the device senses all of the active symptoms and elects to reduce only the symptom with the worst severity. In some embodiments, the device, via sensors, measures the shaking due to RLS of the user and assigns the pattern that relates to the biggest decrease in shaking amplitude of that user where the amplitude is that of the sensor signal and the difference is defined relative to the amplitude observed in the absence of stimulation from the device.

In some embodiments, the sensors coupled to the device are a combination of accelerometers, gyroscopes, IMUs, or other motion-based sensors. In some embodiments, the sensors coupled to the device also include electromyography (EMG) sensors to monitor muscle activation in order to sense tremor severity, rigidity, or movement due to RLS. In some embodiments, the device collects data on the characteristics of the user's symptoms, such as motion amplitude and frequency or muscle activity with sensors contained in the device such as an accelerometer, pressure sensors, force sensors, gyroscope, Inertial Measurement Unit (IMU), or electromyography (EMG) sensors. In some embodiments, the above-mentioned data would be stored through storage components contained within the device. In some embodiments, the above-mentioned data is regularly consolidated for the purpose of larger scale data analysis through a wired or wireless transfer of data to a larger storage location not on the device.

In some embodiments, the actuators are resistive heating elements rather than vibration motors. In some embodiments, the actuators are vibration motors. In some embodiments, the actuators are electromagnets. In some embodiments, the actuators are electropermanent magnets. In some embodiments, the actuators are piezoelectric actuators. In some embodiments, the actuators are voice coil vibration motors. In some embodiments, the actuators are rotating eccentric mass vibration motors in some embodiments, the device is an accessory band to a third-party smartwatch or other wearable computing device. In some embodiments, the device can connect wirelessly (for example via Bluetooth) to the user's smartphone. In some embodiments, the device can be configured to provide contextualized data about the user's condition. For example, the system can correlate symptom onset or degree with time of day, activity level, medication, diet, other symptoms, etc. In some embodiments, this can be accomplished by transmitting extracted sensor signal features to the user's smartphone. An accompanying smartphone application can periodically prompt the user to input other information like activity level, diet, and medication. The application then logs this data with time matched symptom sensor signal features to be reviewed by the user and/or their physician.

In some embodiments, the device can be started by passive sensing of the onset of symptoms such as the on/off phenomenon of Parkinson's patients taking L-dopa. In some embodiments, this can be accomplished by continuously reading sensor data, even while in the “off” state, and then switching to the “on” state when one of the sensor data features, such as amplitude, surpasses a preset threshold value. In some embodiments, the device can be used to amplify an existing but subtle tremor for the purpose of early diagnosis. In some embodiments, this can be accomplished by manually testing a set of stimulation patterns until the tremor is apparent, either visually or as detected by an extracted feature of the sensor data surpassing some preset threshold in some embodiments, this can be accomplished autonomously by inverting the stimulation selection algorithm heuristic such that it converges to the stimulation pattern which maximizes tremor amplitude as measured by the symptom sensor relative to the tremor amplitude measured in the absence of stimulation from the device.

FIG. 1 illustrates a system for mitigating movement disorder in accordance with an embodiment of the present invention. FIG. 1 shows a wearable device 11 interfacing with a user's body 12. The user's body 12 includes proprioceptive nerves 1201, perceived limb position and motion 1202, a nervous system 1203, desired activation control signal 1204, and muscles 1205. The muscles 1205 output electrical activity 14, which is detected by the EMG sensor 1107 in the wearable's sensor suite 1106, and collected as local data 1103. The muscles 1205 also output motion 15, which is detected by the inertial measurement unit (IMU) 1108. The IMI. 1108 measures the body's specific force, angular rate, and orientation, and reports to the processing unit 1101. The processing unit 1101 receives the local data 1103 and executes a local algorithm 1102. Using the local data 1103, the processing unit 110, based on results of the local algorithm 1102, instructs the mechanical transducers 1105 to deliver a specific vibrational stimulus 13. The proprioceptive nerves 1201 detect the vibrational stimulus 13 and send the perceived limb position and motion 1202 to the nervous system 1203. Based on that signal, the nervous system 1203 sends a desired activation control signal 1204 to activate the muscles 1205 in a way that either alters or perpetuates their electrical activity 14 and motion 15. The local data 1103 collected by the sensor suite 1106 continues to be processed by the local algorithm 1102 again, and continues to affect the output of the mechanical transducers 1105. The local data 1103 is also transmitted via the communication module 1104 to a remote processing algorithm 16, and to a remote database 18 for long-term data storage and access by researcher 19. The remote database 18 also receives data from the greater population, or the crowd 17, and sends this data to the remote processing algorithm 16. The remote processing algorithm 16 analyzes the data and returns the results of the analysis both to the processing unit 1101, via the communication module 1104, and also to the crowd 17. In this way, data from the crowd 17 may influence the way that the local algorithm 1102 operates.

In some embodiments, the processing unit 1101 is configured to operate in two modes, a first mode in which it is configured to monitor patent movements passively to detect a movement disorder above a threshold and a second mode in which, following detection of such a movement disorder, the processor is configured to enter into active mitigation of the movement disorder. In some embodiments, processing unit 1101 enters into active mitigation by passive sensing of the onset of symptoms, such as the on/off phenomenon of Parkinson's patients taking L-dopa. In some embodiments, such passive sensing is performed by continuously reading sensor data, even while in the “off” state, and then switching to the “on” state when one of the sensor data features, such as amplitude, surpasses a preset threshold value.

FIG. 2 is an electrical schematic highlighting the main sub-circuits of the system in FIG. 1 . FIG. 2 shows the processing unit 1101, which receives tremor vibration data from the inertial measurement unit 1108 in the inertial measurement unit circuit 24. This data is used by the processing unit 1101 to drive the mechanical transducers 1105 in the mechanical transducer circuit 23 at various frequencies and amplitudes. The entire system receives power from a rechargeable battery 26 in the power/charging circuit 21. The reprogramming/charging port 25 can be used to both recharge the battery 26 and reprogram the processing unit 1101. The power is switched on and off via the on/off button 22.

FIG. 3 is an isometric view of a wearable device in accordance with an embodiment of the present invention FIG. 3 shows the main electronics housing 32 of the device and the band 31 of the device that interfaces with the user's wrist.

FIG. 4 is an exploded isometric view of a wearable device, in which the vibration motors are housed in the band rather than in the main electronics housing, in accordance with an embodiment of the present invention. The mechanical transducers 1105 are housed in the band 31 which interfaces with the user's wrist. Between the top and bottom halves of the housing 321 322, there is a printed circuit board (PCB) 42, a silicone square to insulate the bottom of the PCB 43, and a rechargeable battery 26. The battery 26 includes protection circuitry to protect from overcharging and unwanted discharging. To recharge the battery 26, a magnetic connector 421, coupled to the battery and mounted in the housing, is inserted into the PCB 42. The magnetic connector 421 couples to a mating connector from an external charger, so that the battery 26 can be conveniently configured for charging by the external charger. The magnetic connector 421 allows patients who have difficulty performing tasks that require fine motor skills to easily charge the device with a magnetic charging cable. The device is intended to work after the patient turns the device on by pressing the single, large button 323 on top of the electronic housing top 321. The button is provided for ease of use by a patient whose fine motor control is affected by a neurological movement disorder.

FIG. 5 is an isometric view of a wearable device, in which the device includes a loop mechanism SI to allow single handed adjustment of the band 31 on the user's wrist, in accordance with an embodiment of the present invention. FIG. 5 shows the main electronics housing 32, the band 31 as it looks when worn on the user's wrist, and an adjustment mechanism 51 that is integrated into the main electronics housing 32.

FIG. 6 shows an embodiment of the present invention worn on a hand viewed from above FIG. 6 shows the main electronics housing 32 and the band 31 that interfaces with the user's wrist.

FIG. 7 shows an embodiment of the present invention worn on a hand viewed from the side. FIG. 7 shows the main electronics housing 32, the band 31 that interfaces with the user's wrist, and the on/off button 323 that a patient may use to begin/stop the vibrational stimulation. The on/off button 323 is integrated into the main electronics housing 32.

FIG. 8 shows a testing configuration for the wearable medical device, which may be used for more rigorous data collection, in accordance with an embodiment of the present invention. FIG. 8 shows the main electronics housing 32 and the band 31 that interfaces with the user's wrist. These are connected to a data logging apparatus 81 which collects and stores data. Data can continue to be collected and stored over a larger time scale than on the device alone, as this testing configuration is equipped with a larger processor and storage capacity. At the time of analysis, more complex and computationally heavy data analysis is possible on the collected data stored in the data logging apparatus 81 utilizing the larger processor.

FIG. 9 illustrates a wearable device for mitigating movement disorder, in which the device is an accessory to a third-party smartwatch or other wearable computing device 91, in accordance with an embodiment of the present invention. In such an embodiment, some or all of the computation 912 and sensing 911 are offloaded to the third-party wearable device 91. The third-party device then sends a set of motor commands wirelessly 94 (over Bluetooth for example 913 925) to a processing unit 1101 on the accessory band 92. This processing unit 1101 interfaces with the transducers 1105 on the band to execute the desired motor commands. In this embodiment, the accessory band 92 has its own battery 924. In some embodiments, the band also has its own specialized sensors 923 (such as electromyography sensors), the signals of which are communicated to the third-party processing unit 912 via the accessory processing unit 1101, and wireless communication 913 925 94. Data may also be logged to the user's smartphone 93 over the same wireless connection 94.

FIG. 10 shows a side view of a wearable device, which is as an accessory band for a third-party smartwatch or other wearable computing device, in accordance with an embodiment of the present invention. It shows the main electronics housing 32 and the band 31 which contains the mechanical transducers 1105. The band 31 interfaces with the user's wrist. This view illustrates an example placement of the accessory battery 925 and processing unit 1101.

FIG. 11 shows a process by which a raw sensor input may be used to compute a set of stimulation parameters in accordance with an embodiment of the present invention. The stimulation parameters are continuously updated in closed loop. These parameters can include any quantities used to define a stimulation waveform such as frequency, amplitude, phase, duty cycle, etc. At each iteration of the update loop, the current stimulation parameters 111 and raw sensor input 112 are used to filter out transducer/sensor crosstalk 113 either by using knowledge of the output waveform to subtract from the sensed waveform or by using knowledge of the timing of the output waveform to limit sensing to the “off” phases of a pulsing stimulation. This filtering subsequently allows for feature extraction 114 of the raw sensor input 112. The stimulation selection algorithm 115 then uses the current stimulation parameters 111 and the extracted features 114 to select new stimulation parameters 116. This process is illustrated in greater depth in FIG. 13 . When the process repeats, the previously new stimulation parameters 116 become to the current stimulation parameters 111.

FIG. 12 shows a feature extraction process 114 in accordance with an embodiment of the present invention. This process takes in a filtered sensor signal 113, as described with respect to FIG. 11 , and extracts temporal 1141 1142 1143 and/or spectral features 1144. Examples of common temporal features include the minimum value, the maximum value, first three standard deviation values, signal energy, root mean squared (RMS), zero crossing rate, principal component analysis (PCA), kernel or wavelet convolution, or autoconvolution. Examples of common spectral features include the Fourier Transform, fundamental frequency, (Mel-frequency) Cepstral coefficients, the spectral centroid, and bandwidth. Features are extracted with standard digital signal processing techniques onboard the main processing unit of the device. The set of collected features is then fed into the stimulation selection algorithm 115.

FIG. 13 shows a stimulation optimization algorithm 115 in accordance with an embodiment the present invention. The stimulation selection algorithm takes in the extracted features 114 and the current stimulation parameters 111 and uses them to determine the set of new stimulation parameters 116. The process by which the new parameters are determined is an optimization 1151 to minimize the symptom severity. Given that there is no analytical model for the symptom's response to stimulation patterns, this optimization is inherently model free. Examples of model free policy optimization techniques are argmin (or minimization over the set of input arguments), Q-learning, neural networks, genetic algorithms, differential dynamic programming, iterative quadratic regulator, and guided policy search. Descriptions of some such algorithms can be found in Deisenroth, M. P. (2011), “A Survey on Policy Search for Robotics,” Foundations and Trends in Robotics, 2(1-2), 1-142. doi:10.1561/2300000021; and Beasley, D., Bull, D. R., & Martin, R. (1993), “An Overview of Genetic Algorithms: Part 1, Fundamentals,” 1-8, (herein incorporated, in their entirety, by reference).

In an example, an extracted feature may be the amplitude of the tremor and the set of current stimulation parameters could be a stimulation frequency and amplitude. A stimulation selection algorithm can then compare the tremor amplitude observed with the current set of stimulation parameters to the tremor amplitude observed with a previous set of stimulation parameters to determine which of the two sets of stimulation parameters resulted in the lowest tremor amplitude. The set with the lowest resulting tremor amplitude could then be used as the baseline for the next iteration of the stimulation selection algorithm which would compare it to a new set.

Two example stimulation selection algorithms that may be used in embodiments follow:

Algorithm 1 Determine Optimal Vibration Motor State Input: Feed of x, y, z accelerometer data Output: Output state which minimizes tremor magnitude 1: AmplitudeStates = {A₁, A₂, . . . , A_(n)} = {A}_(n) 2: FrequencyStates = {F₁, F₂, . . . , F_(m)} = {F}_(m) 3: OutputStates = {A × F}_(n×m) 4: TremorResponses = {0}_(n×m) 5: 6: for State in OutputStates do 7:  Output ← State 8:  TremorResponse{State} ← ReadAccelerometer 9: $\left. {OptimalState}\leftarrow{\underset{{(A)},{(F)}}{\arg\min}{TremorResponses}} \right.$

Algorithm 2 Q-learning Algorithm Input: Feed of x, y, z accelerometer data Output: Output state which minimizes tremor magnitude  1: AmplitudeStates = {A₁, A₂, . . . , A_(n)} = {A}_(n)  2: FrequencyStates = {F₁, F₂, . . . , F_(m)} = {F}_(m)  3: OutputStates = {A × F}_(n×m) = S  4: Choices = {IncreaseAmplitude, IncreaseFrequency} = C  5: QTable = Q: S × C → R  6: for Epoch in MaxEpochs do  7:  for s in OutputStates do  8:   for e in Choices do  9:    r ← ReadAccelerometer 10:     $\left. {Q\left( {s,e} \right)}\leftarrow{{\left( {1 - a} \right) \cdot {Q\left( {s,e} \right)}} + {\alpha \cdot \left( {r + {{\gamma \cdot \min\limits_{k \in C}}{Q\left( {{s + 1},k} \right)}}} \right)}} \right.$ 11: $\left. {OptimalState}\leftarrow{\underset{S}{\arg\min}Q} \right.$

In some embodiments, the structure of the output stimulation pattern may be a weighted average of optimized patterns corresponding to each symptom where the weights are proportional to the symptom severity relative to the other observed symptoms. In some embodiments, the structure of the output stimulation pattern may just be the pattern optimized to reduce the most severe symptom.

FIG. 14 shows a neurological signal cancelling system, illustrating how the wearable 11 device and body 12 interact, in accordance with an embodiment of the present invention. The system comprises of the user's nervous system 1203, which sends control signals 141 to the body 12. The wearable 11 senses the body's movement and sends an opposing control signal 142 which is defined by the output of the active noise cancellation algorithm 143. The control signals 141, 142 undergo a signal cancelling process within the nervous system of the user 1203, which results in a smoother perceived motion signal 144.

FIG. 15 shows a process in which the raw sensor input 112 may be processed using active noise cancellation to compute a set of stimulation parameters, in accordance with an embodiment of the present invention. In FIG. 15 , the suite of movement disorder sensors 1106 within the device 11 quantify the real limb position and motion 1206 to produce a raw sensor input 112, which is then filtered using both a noise filter 113 and a movement disorder filter 151. The noise filter 113 may use either knowledge of the output waveform to subtract from the sensed waveform or knowledge of the timing of the output waveform to limit sensing to the “off” phases of a pulsing stimulation. The movement disorder filter 151 uses a 3-15 Hz bandpass filter to eliminate any other signal components not caused by a movement disorder. The resultant filtered sensor data 152 is then fed to the active noise cancellation processor 153, which generates the anti-tremor stimulation signal 154. The active noise cancellation processor 153 is described in further detail in connection with FIGS. 16 and 17 . The device 11 uses vibrational stimulus 13 to transmit the anti-tremor stimulation signal 154 to the proprioceptors 1201 of the user's body. Information on the body's reaction to the anti-tremor stimulation signal can be found in further detail in connection with FIG. 1 .

FIG. 16 shows one exemplary embodiment of the process of anti-tremor stimulation signal 154 generation by the active noise cancellation (ANC) processor 153. The ANC processor 153 takes the resulting filtered sensor data 152 of FIG. 15 as input, which is then transformed into the frequency domain by applying a Fourier Transform 1531. By definition, the fundamental frequency, ω_(max), the frequency having the greatest amplitude, is selected through argmax 1532 of the frequency domain data from the Fourier Transform 1531, and the output is used as the center of a bandpass filter 1533 to ensure an accurate time delay calculation 1534. For example, if the fundamental frequency is calculated to be 10 Hz, then one exemplary embodiment of the bandpass filter 1533 may be set at 8-12 Hz. The fundamental frequency is also used to calculate the time delay 1534 necessary to achieve a 180-degree phase. It is important to note that a phase delay of 180-degrees of a periodic signal is equivalent to a signal inversion. As a result, feedback with a 180-degree phase delay would behave as negative feedback. Time delay to achieve a 180-degree phase is equal to

$\frac{1}{2*{frequency}}$

This filtered and delayed signal is output as the anti-tremor stimulation signal 154. This process can be repeated for the 2^(nd) through N^(th) fundamental frequencies.

FIG. 17 shows another exemplary embodiment of the process of anti-tremor stimulation signal 154 generation by the ANC processor 153. The ANC processor 153 takes filtered sensor data 152 from an inertial motion unit (IMU) and calculates the resultant limb acceleration 171. The limb acceleration 171, in the time domain, is then transformed into the frequency domain by applying a Fourier Transform 1531 allowing the ANC processor 153 to extract the peak frequencies 172 of the limb acceleration using general peak finding algorithms, which take a set of data and return a set of local maxima, or peaks, such that the data points on either side of the peaks are less than said maxima. The ANC processor 153 selects the window size 173 of the acceleration 171 by use of one of two methods.

The first method 174 uses the lowest peak frequency to calculate the window size. Selecting the lowest peak frequency ensures that all the relevant features of the limb acceleration 171 are captured in the window and able to be properly reproduced when generating the anti-tremor stimulation signal 154. This method involves inverting the lowest peak frequency, which corresponds to the lowest frequency feature in the limb acceleration 171, and converting it into the time domain [Hz=1/s]. In FIG. 17 , the lowest peak frequency is 3 Hz, so the window size is ⅓s.

The second method 175 uses a window size of fixed length. The acceleration data captured in the selected fixed window size is then inverted and becomes the anti-tremor stimulation signal 154 output. The lower bound of acceptable window size is found using the first method 174, the time domain conversion of the lowest peak frequency. A window smaller than this would fail to capture all of the relevant features of the limb acceleration 171. Theoretically, there is no upper bound of acceptable window size 173, but in practice, the upper bound will depend on the available memory of the device 11.

FIG. 18 is a pair of renderings 181 182 by a tremor patient of an Archimedes spiral under conditions without and with treatment by a device in accordance with an embodiment of the present invention. The spiral tracing test allows doctors to gain insight on the frequency, amplitude, and direction of their patients' tremors. It can also inform the doctor of abnormal movement of hypokinesia, dystonia, and tremor. The task requires the patient to continuously trace the Archimedes spiral Patients who have tremors will have difficulty following the spiral and will trace off the spiral line resulting in a disordered spiral 181. Wearing a device in accordance with an embodiment of the present invention, the patient is able to trace the spiral more accurately resulting in a smoother spiral 182.

FIG. 19 illustrates an embodiment of a simple non-convex gradient descent optimization used in an embodiment of the present invention for symptom reduction by searching over the parameter configuration space. It is a graphical representation of the stimulation selection algorithm 193 associated with the present invention. The algorithm 193 moves through the stimulation parameter space 192 and attempts to minimize symptom severity 191. The movement through the stimulation parameter space involves trying different sets of stimulation parameters and comparing their resulting symptom severities as quantified by their respective sensors. The algorithm attempts to minimize symptom severity by testing different sets of parameters until an optimal set for minimizing symptom severity is found.

Alternative benchtop versions of the device can be used to elicit tremors in Parkinson's patients for the purposes of early detection. This is done using the same mechanisms as in reducing tremor but using an inverted stimulation parameter search heuristic. User testing has shown that for each patient, there exists a stimulation pattern which when applied to the Parkinson's patient with very slight tremor will produce a very large tremor. This effect does not occur in users who do not have Parkinson's Disease. This could be used for earlier detection and diagnosis of Parkinson's Disease which can be difficult to diagnose.

FIGS. 20 and 21 each show a power spectral density (PSD) plot of the postural tremor of a Parkinson's Disease and Essential Tremor patient, respectively, with and without the use of a device in accordance with an embodiment of the present invention. The data was taken by asking each patient to hold his or her hand out for 10 seconds, with and without the device. In FIGS. 20 and 21 , tremor amplitude is compared with and without the device.

The following describes a test case of an embodiment of the present invention. Participants were asked to trace a printed Archimedes Spiral, a common test used to diagnose Parkinson's, with and without the device, as shown in FIG. 18 . The results were measured by using image processing software to evaluate the accuracy of the traced spirals. In the first round of testing, the device was tested on around 20 participants with Parkinson's and 1 participant with a resting tremor. The majority of the participants, however, either did not experience tremors or were already being treated for Parkinson's and only experienced slight tremors. It was observed that the reduction in tremor severity was strongly correlated to the initial tremor severity. That is, patients with minimal tremors experienced minimal benefit while patients with more extreme tremors experienced more dramatic benefit. The participant with the most severe resting tremor, caused by Parkinson's Disease, saw the most improvement in performance as shown in FIG. 20 . Another participant with a resting tremor, caused by Essential Tremor, also showed significant improvement as shown in FIG. 21 . The results were repeatable with both of these participants. Participants who suffered from rigidity observed that they had a larger range of movement in their hands and completed their spiral tests faster with the device than without.

While the above embodiments reference accelerometers, vibration motors, microUSB, and wristbands the invention is not limited to such implementations. Additionally, the above embodiments are not intended to limit the scope of the invention. For example, various modifications and variations of interfaces, types of electromyography sensors, gyroscopes, inertial measurement units, piezoelectrics, electromagnets, electropermanent magnets, pneumatics, voice coils, hydraulics, resistive heating elements should be included. The scope of form factors should also include headbands, collars, anklets, armbands, and rings. The scope of electrical interfaces should include Thunderbolt cables, USB, USB C, microUSB, wireless communication, wireless charging, and Bluetooth communication.

The present invention may be embodied in many different forms, including, but in no way limited to, computer program logic for use with a processor (e.g., a microprocessor, microcontroller, digital signal processor, or general purpose computer), programmable logic for use with a programmable logic device (e.g., a Field Programmable Gate Array (FPGA) or other PLD), discrete components, integrated circuitry (e.g., an Application Specific Integrated Circuit (ASIC)), or any other means including any combination thereof.

Computer program logic implementing all or part of the functionality previously described herein may be embodied in various forms, including, but in no way limited to, a source code form, a computer executable form, and various intermediate forms (e.g., forms generated by an assembler, compiler, networker, or locator.) Source code may include a series of computer program instructions implemented in any of various programming languages (e.g., an object code, an assembly language, or a high-level language such as Fortran, C, C++, JAVA, or HTML) for use with various operating systems or operating environments. The source code may define and use various data structures and communication messages. The source code may be in a computer executable form (e.g., via an interpreter), or the source code may be converted (e.g., via a translator, assembler, or compiler) into a computer executable form.

The computer program may be fixed in any form (e.g., source code form, computer executable form, or an intermediate form) either permanently or transitorily in a tangible storage medium, such as a semiconductor memory device (e.g., a RAM, ROM, PROM, EEPROM, or Flash-Programmable RAM), a magnetic memory device (e g., a diskette or fixed disk), an optical memory device (e.g., a CD-ROM), a PC card (e.g., PCMCIA card), or other memory device. The computer program may be fixed in any form in a signal that is transmittable to a computer using any of various communication technologies, including, but in no way limited to, analog technologies, digital technologies, optical technologies, wireless technologies, networking technologies, and internet working technologies. The computer program may be distributed in any form as a removable storage medium with accompanying printed or electronic documentation (e.g., shrink wrapped software or a magnetic tape), preloaded with a computer system (e.g., on system ROM or fixed disk), or distributed from a server or electronic bulletin board over the communication system (e.g., the Internet or World Wide Web).

Hardware logic (including programmable logic for use with a programmable logic device) implementing all or part of the functionality previously described herein may be designed using traditional manual methods, or may be designed, captured, simulated, or documented electronically using various tools, such as Computer Aided Design (CAD), a hardware description language (e.g., VHDL or AHDL), or a PLD programming language (e.g., PALASM, ABEL, or CUPL).

While the invention has been particularly shown and described with reference to specific embodiments, it will be understood by those skilled in the art that various changes in form and detail may be made therein without departing from the spirit and scope of the invention as defined by the appended clauses. While some of these embodiments have been described in the claims by process steps, an apparatus comprising a computer with associated display capable of executing the process steps in the claims below is also included in the present invention. Likewise, a computer program product including computer executable instructions for executing the process steps in the claims below and stored on a computer readable medium is included within the present invention.

The embodiments of the invention described above are intended to be merely exemplary; numerous variations and modifications will be apparent to those skilled in the art. All such variations and modifications are intended to be within the scope of the present invention as defined in any appended claims. 

What is claimed is:
 1. A wearable device for mitigating a movement disorder symptom of a user, comprising: a band; a processing unit disposed in the band; and a vibration motor disposed in the band and in communication with the processing unit, wherein the processing unit is configured to: receive a signal from a third-party wearable device; and activate the vibration motor to provide a vibrational output to a portion of a user based on the signal.
 2. The wearable device of claim 1, wherein the third-party wearable device is a smartwatch.
 3. The wearable device of claim 1, wherein the signal is generated from a sensor suite of the third-party wearable device, the sensor suite of the third-party wearable device configured to transmit sensor data related to a movement disorder symptom of the user.
 4. The wearable device of claim 1, wherein the processing unit is further configured to convert the signal into a stimulation waveform; and activate the vibration motor to provide a vibrational output to a portion of the user based on the stimulation waveform.
 5. The wearable device of claim 1, wherein the band is configured to couple to a housing of the third-party wearable device.
 6. The wearable device of claim 1, wherein the processing unit is configured to: offload one or more processes of to the third-party wearable device; and receive a motor command from the third-party wearable device, wherein the processing unit activates the vibration motor based on the motor command.
 7. The wearable device of claim 1, wherein the band further comprises a sensor, the sensor configured to generate sensor output relating to a movement disorder of a user.
 8. The wearable device of claim 7, further comprising a plurality of sensors disposed in the band, each sensor of the plurality of sensors positioned around a circumference of the band.
 9. The wearable device of claim 1, further comprising a plurality of vibrational motors disposed in the band, each vibration motor of the plurality of vibration motors positioned around a circumference of the band.
 10. The wearable device of claim 1, wherein the band further comprises a battery configured to power the processing unit and the vibration motor.
 11. The wearable device of claim 1, wherein the third-party wearable device is in communication with a smartphone.
 12. A method of mitigating a movement disorder symptom of a user, comprising: receiving, at a processing unit disposed within a band, a signal from a third-party wearable device; activating, by the processing unit, a vibration motor based on the signal from the third-party wearable device, wherein the vibrational motor is disposed within the band and connected to the processing unit; and providing a vibrational output generated from the vibration motor to a portion of a user to mitigate a movement disorder symptom of the user.
 13. The method of claim 12, further comprising: generating sensor output related to a movement disorder of the user from a sensor of the third-party wearable device; and transmitting, from the third-party wearable device to the processing unit, a signal for a motor command of the vibration motor.
 14. The method of claim 12, further comprising: generating sensor output from a sensor of the band; calculating, at the processing unit, a vibrational output based on the sensor output; and activating, by the processing unit, the vibration motor to provide the vibrational output to the portion of the user.
 15. The method of claim 12, further comprising: generating sensor output from a sensor of the band; transmitting the sensor output to the third-party wearable device; calculating, at the third-party wearable device, a vibrational output; transmitting the vibrational output from the third-party wearable device to the processing unit; and activating, by the processing unit, the vibration motor based on the vibrational output.
 16. The method of claim 12, wherein the band is coupled to a housing of the third-party wearable device.
 17. The method of claim 12, wherein the band comprises a battery configured to power the vibration motor and the processing unit.
 18. The method of claim 12, wherein the vibrational output includes a stimulation waveform.
 19. The method of claim 12, wherein the third-party device is a smartwatch.
 20. The method of claim 12, wherein the third-party wearable device is in communication with a smartphone. 